Tissue and other body structures may be protected using a dry, free-flowing, sterilized mixture of chitosan particles and oxidized polysaccharide particles in sealed packaging. The mixture may assist in returning an injured, inflamed or surgically repaired surface to a normal state, e.g., through one or more healing mechanisms such as modulation of an inflammatory response, phagocytosis, mucosal remodeling, reciliation or other full or partial restoration of normal function.
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1. A composition comprising a dry, free-flowing, sterilized mixture of separate rehydratable particles comprising about 20 to about 95 wt. % of chitosan particles containing amino groups and about 80 to about 5 wt. % of oxidized polysaccharide particles containing aldehyde groups in sealed packaging, wherein the amino group functionality and molecular weight of the chitosan and the aldehyde group and molecular weight of the oxidized polysaccharide are such that the mixture of chitosan particles and separate oxidized polysaccharide particles are rehydratable in situ when removed from the sealed packaging and applied in a dry state to a surgical tissue site or wound moistened with bodily fluids such that the mixture of chitosan particles and separate oxidized polysaccharide particles will adhere to such tissue site or wound and will adhere to one another by inter-particle crosslinking reaction of amino groups on the chitosan particles with aldehyde groups on the polysaccharide particles, wherein the dry, free-flowing, sterilized mixture of chitosan and oxidized polysaccharide particles contains less than 10% wt. % water.
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This application is a continuation of application Ser. No. 14/324,889 filed Jul. 7, 2014, now allowed, which is a continuation of application Ser. No. 12/429,127 filed Apr. 23, 2009, now U.S. Pat. No. 8,802,652 B2, and which claims priority from U.S. Provisional Application Ser. No. 61/047,580 filed Apr. 24, 2008, the disclosures of each of which are incorporated herein by reference.
This invention relates to polysaccharides and to materials for use in the body.
Certain polysaccharide materials have been used for surgical repair or drug delivery. Documents relating to such materials include U.S. Pat. No. 5,820,608 (Luzio et al.), U.S. Pat. No. 5,993,846 (Friedman et al.), U.S. Pat. No. 6,123,965 (Jacob et al.), U.S. Pat. No. 6,342,251 B1 (lilum et al.), U.S. Pat. No. 6,706,690 B2 (Reich et al.), U.S. Pat. No. 6,835,389 B1 (Dohi et al.) and U.S. Pat. No. 7,195,675 B2 (Okazaki et al.); U.S. Patent Application Publication No. US 2005/0208122 A1 (Allen et al.); Published PCT Application No. WO 93/21906 A (Brown University Research Foundation) and Weng et al., Rheological Characterization of in Situ Crosslinkable Hydrogels Formulated from Oxidized Dextran and N-Carboxyelhyl Chilosan, Biomacromolecules, 8, 1109-1115 (2007). Polysaccharide gels may be used as tissue sealants in ear, nose and throat (ENT) procedures.
In order to avoid undue degradation during storage, it is desirable to package polysaccharide gel materials in dry form (e.g., as a powder or sponge) and rehydrate the material just prior to use. Rehydration sometimes presents difficulties. Some rehydrated materials provide gels or sponges with poor physical properties. The physical properties of a rehydrated gel may in some instances be improved via in situ crosslinking, but there may be an increased risk that an overly crosslinked gel will inadvertently be dislocated (e.g., aspirated) into the lungs or elsewhere in the form of large solid chunks. Some external crosslinking agents may damage tissue, or may cause residence times which are excessively long or difficult to control.
The present invention provides, in one aspect, a composition comprising free-flowing rehydratable particles of substantially collagen-free dehydrothermally crosslinked polysaccharide. In one exemplary embodiment the particles comprise a cellulose such as carboxymethylcellulose (CMC), and may provide a rehydrated gel having one or more desirable properties including rapid, clump-free rehydration; thixotropic behavior when sprayed or injected; high viscosity and cohesive gel character once in place; controllable biodegradation properties, resistance to premature biodegradation and an ability to break down or be dislocated without producing large solid chunks. In another exemplary embodiment the particles comprise a blend of CMC and chitosan, and may provide a rehydrated gel having one or more desirable properties like those provided by the disclosed CMC rehydrated gels, together with one or more additional desirable properties including inherent antimicrobial (e.g., bactericidal) behavior; hemostatic ability or the promotion of wound healing. The disclosed rehydrated gels may assist in returning an injured, inflamed or surgically repaired surface (e.g., a mucosal tissue surface) to a normal state, e.g., through one or more healing mechanisms such as modulation of an inflammatory response, phagocytosis, mucosal remodeling, reciliation or other full or partial restoration of normal function.
The invention provides in another aspect an implantable article comprising a rehydratable porous sponge comprising substantially collagen-free dehydrothermally crosslinked polysaccharide. The sponge may be packaged and sold in compressed form, may be trimmed to a desired size or shape for implantation at a treatment site, and may be rehydrated prior to or following implantation. Exemplary embodiments of the disclosed sponge include sponges made from CMC and sponges made from blends of CMC and chitosan.
The invention provides in another aspect a method for making a polysaccharide gel-forming composition, which method comprises providing a substantially collagen-free polysaccharide solution, drying the solution to form a powder, and dehydrothermally crosslinking the powder to form free-flowing particles that will provide a polysaccharide gel when rehydrated. Exemplary embodiments of the disclosed method include methods which make powders from CMC and from blends of CMC and chitosan.
The invention provides in another aspect a method for making an implantable article, which method comprises providing a substantially collagen-free polysaccharide solution, lyophilizing the solution to form a dried porous sponge, dehydrothermally crosslinking the sponge, and optionally compressing the sponge, thereby forming an implantable article which will form a polysaccharide sponge when rehydrated. Exemplary embodiments of this disclosed method include methods which make sponges from CMC and from blends of CMC and chitosan.
The invention provides in another aspect a method for treating tissue and other body structures, which method comprises applying thereto a gel or sponge comprising rehydrated substantially collagen-free dehydrothermally crosslinked polysaccharide.
Rehydration may present additional difficulties. Some dry powder materials are prone to clumping when combined with water. The clumps can be difficult to disperse and may plug syringes, cannula or spray nozzles. The invention provides, in yet another aspect, a method for converting a dry powdered composition to a gel, which method comprises dispersing free-flowing polysaccharide particles in a biocompatible water-miscible polar dispersant, and combining the resulting dispersion with sufficient aqueous solvent for the particles to convert them to a cohesive hydrogel. The polysaccharide particles may be crosslinked or uncrosslinked, and if crosslinked the crosslinking may be dehydrothermal crosslinking or crosslinking carried out using a separate crosslinking agent. The polysaccharide particles may be substantially collagen-free. The polysaccharide particles may be substantially a single polysaccharide or a blend of two or more polysaccharides. The cohesive hydrogel may be formed without visible clumps of unhydrated polysaccharide. The disclosed method may be followed by a treatment method including a step of injecting or spraying a layer of the cohesive hydrogel onto tissue (e.g., mucosal tissue) or other body structures.
Like reference symbols in the various figures of the drawing indicate like elements. The elements in the drawing are not to scale.
The following detailed description describes certain embodiments and is not to be taken in a limiting sense. All weights, amounts and ratios herein are by weight, unless otherwise specifically noted. The terms shown below have the following meanings:
The term “adhesion” refers to the sticking together of a body structure or prosthetic material to tissue, to the sticking together of tissue to tissue with which it is in intimate contact for extended periods, or to the formation of tissue that connects body structures, prosthetic materials or tissues to one another across a normally open space.
The term “antimicrobial” refers to an ability to cause greater than a 90% numeric reduction (viz., at least a 1-log order reduction) in a population of one or more of Staphylococcus aureus, Pseudomonas aeruginosa, Streplococcus pneumonia, Haemophilus influenzae or Moraxella catarrhalis.
The terms “attached” and “adhered” when used in reference to a bacterial biofilm and a surface mean that the biofilm is established on and at least partially coats or covers the surface, and has some resistance to removal from the surface. As the nature of this relationship is complex and poorly understood, no particular mechanism of attachment or adherence is intended by such usage.
The term “bacterial biofilm” means a community of bacteria attached to a surface, with the organisms in the community being contained within an extracellular polysaccharide (EPS) matrix produced by the bacteria.
The term “biocompatible” when used in reference to a substance means that the substance presents no significant deleterious or untoward effects upon the body.
The term “biodegradable” when used in reference to a substance means that the substance will degrade or erode in vivo to form smaller chemical or physical species. Such degradation process may be enzymatic, chemical or physical.
The term “bioresorbable” when used in reference to a substance means that the substance is capable of being absorbed by the body.
The term “cohesive” when used in reference to a liquid or gel means that the liquid or gel when placed on a level surface will tend to (but need not in all cases) stick to itself and form a unitary mass.
The term “comminuted” when used in reference to a particulate material means that the particles have been fractured and reduced in size by cutting, grinding, pulverizing, triturating or other particle fracturing process employing externally-applied force.
The term “conformal” when used in reference to a composition applied to tissue or other body structure means that the composition can form a substantially continuous layer over an area to which the composition has been applied.
The terms “detaching”, “removing” and “disrupting” when used in reference to a bacterial biofilm attached or adhered to a surface mean that at least a significant amount of the biofilm initially present on the surface no longer is attached or adhered to the surface. No particular mechanism of detachment, removal or disruption is intended by such usage.
The term “fluid” when used in reference to a substance means that the substance is a liquid having a loss modulus (G″) greater than its storage modulus (G′) and a loss tangent (tan δ) greater than 1.
The term “gel” when used in reference to a substance means that the substance is deformable (viz., is not a solid), G″ is less than G′ and tan δ is less than 1.
The term “gelation” when used with respect to formation of a gel layer means the time at which G″ equals G′ and tan δ equals 1.
The term “hemostat” means a device or material which stops blood flow.
The term “hydrogel” when used in reference to a gel means that the gel is hydrophilic and contains water.
The term “hydrated” when used in reference to a device or substance means that the device or substance contains uniformly distributed chemically-bound water. A “fully hydrated” device or substance is incapable of taking up additional water of hydration. A “partially hydrated” device or substance is capable of taking up additional water of hydration.
The term “inner ear” means the semicircular canals and cochlea.
The term “middle ear” means the region defined by the tympanic membrane, interior structures such as the ossicular chain, the surrounding lining and bordering structures such as the mastoid.
The term “mucoadhesive” when used in reference to a device or substance means that the device or substance will adhere to the mucus covering epithelia.
The term “nasal or sinus cavities” refers to the various tissues defining the normally air-filled passages and chambers within the nose and sinus including but not limited to the nostrils or nares, the nasal concha or turbinates, the frontal, ethmoid, sphenoid and maxillary sinuses, the sinus ostia and the nasopharnyx.
The term “polysaccharide” includes derivatives of polysaccharides and modified polysaccharides, as well as derivatives of individual polysaccharide species and modified individual polysaccharide species. For example, the term “carboxymethylcellulose” includes carboxymethylcellulose derivatives and modified carboxymethylcelluloses, the term “chitosan” includes chitosan derivatives and modified chitosans, and the term “starch” includes starch derivatives and modified starches.
The term “protective” when used in reference to a layer of a composition atop tissue or other body structure means that the layer may assist in returning an injured, inflamed or surgically repaired tissue surface to a normal state, e.g., through one or more healing mechanisms such as modulation of an inflammatory response, phagocytosis, mucosal remodeling, reciliation or other full or partial restoration of normal function.
The term “residence time” when used in reference to a protective gel layer atop tissue or other body structure means the time period during which the gel layer or portion thereof remains in place in vivo under gross observation.
The term “solvating” means to form a solution or dispersion containing a solvent or other carrier within which a solute is dissolved or suspended.
The term “substantially collagen-free” means containing a sufficiently low amount of collagen so as not to pose a potential risk of transmission of or infection with bovine spongiform encephalopathy (BSE) or variant Creutzfeldt-Jakob disease (vCJD).
The term “thin” when used in reference to a protective layer atop tissue or other body structure means having an average thickness less than about two millimeters.
Referring to
The applied rehydrated gel may fill the treatment site (e.g., a nasal or sinus cavity, or an opening, recess, passageway or joint in a portion of the limbs or spinal column), in which case the disclosed gel layer may be very thick and not exposed to air or other nearby gases, and with differing thicknesses throughout the layer. The disclosed rehydrated gel may also be applied as a thin film or other conformal coating in which case the disclosed gel layer may be relatively thin and exposed to air or other nearby gases, and with a substantially uniform thickness throughout the layer. The rehydrated gel composition provides a protective layer which may be viscous, elastic or viscoelastic. The protective layer desirably adheres to mucosal or other natural tissues (e.g., cartilage or bone) at the treatment site and resists detachment or other disruption until natural degradation or resorption of the gel layer takes place, e.g., after a residence time in vivo of from one day to a few (e.g., 2, 3 or 4) days, weeks or months. Meanwhile bacterial recolonization or reinfection may be significantly reduced or prevented, and improved healing and reciliation may take place. The protective gel layer may provide various therapeutic advantages including but not limited to bacterial adhesion repellence, anti-infective properties, local immune modulation, tissue protection, reduction or elimination of pain or bleeding, reduction in inflammation, optimization of environment for ciliary regrowth, reduction in adhesions to critical anatomy, and the like. These advantages may arise due to a variety of mechanisms including a) killing bacteria, b) inhibiting bacterial colonization, c) inhibiting the adherence of bacteria to tissue, d) reducing tissue morbidity or abscess formation, e) reducing or preventing disease recurrence (for example, specifically reducing the chronic inflammation related to bacterial toxin and EPS), f) coating and protecting tissue during healing, such as by maintenance of a moist wound which promotes platelet aggregation, or by closure of a dry wound without excessive scabrous formation, g) hemostasis, h) optimizing the environment for reciliation of the mucosa, i) speeding the growth or regrowth of cilia and j) delivering therapeutic agent(s) to the treatment site. Desirably the protective gel layer will adhere to a portion of the mucosa while leaving the cilia in unadhered portions free to undergo natural rhythmic cilia motion (viz., cilia beating), will if desired also deliver antimicrobial agents or additional therapeutic agents, and desirably will discourage or prevent bacteria from adhering to the treatment site.
A wide variety of polysaccharides may be employed in the disclosed rehydratable gel composition and in the disclosed sponge. In addition to celluloses and chitosans, exemplary polysaccharides include agars, alginates, carrageenans, chitins, chondroitin sulfates, dextrans, galactomannans, glycogens, hyaluronic acids, starches and other biocompatible polysaccharides capable of being formed into a hydrogel or self-supporting sponge. Derivatives (including oxidized polysaccharides and salts) and mixtures of polysaccharides (including derivatives) may also be used. Compositions containing mixtures of polysaccharides are especially desirable in order to form hydrogels and sponges whose properties would not be provided using a single polysaccharide. For example compositions containing CMC and chitosan provide an especially desirable set of properties. Other desirable compositions include those containing chitosan together with an alginate, hyaluronic acid or chondroitin sulfate. The chosen polysaccharide(s) desirably can be crosslinked via a dehydrothermal condensation reaction as described in more detail below, and one or all of the polysaccharides in a mixture of polysaccharides may be so crosslinked. The chosen polysaccharide(s) also desirably are water soluble or may be rendered so, e.g., by suitable acidification.
A variety of celluloses may be employed in the disclosed rehydratable gel and in the disclosed sponge, including CMC, methylcellulose, ethylcellulose, hydroxypropyl cellulose, hydroxypropyl methyl cellulose and hemicellulose, as well as derivatives thereof including oxidized celluloses. Exemplary cellulosic materials may be obtained from a variety of commercial sources including Dow Wolff Cellulosics (for example, the WALOCEL™ CRT line of sodium carboxymethylcellulose products), Hercules, Inc. (for example, the AQUALON™ line of cellulose gum and carboxymethylcellulose products) and Sigma-Aldrich Co. (for example, No. C4021 microgranular cellulose). The cellulosic material desirably is obtained in particulate form, for example, as free-flowing granules whose average particle diameter is less than about 1 mm, less than about 100 μm, about 1 to about 80 μm, or less than 1 μm.
A variety of chitosans may be employed in the disclosed rehydratable gel and in the disclosed sponge. Exemplary unmodified chitosans and their salts (including citrate, nitrate, lactate, phosphate, chloride and glutamate salts) may be obtained from a variety of commercial sources including KitoZyme S. A., Fluka Chemie AG, the NovaMatrix unit of FMC BioPolymer AS and Sigma-Aldrich Co. Chitosan may also be synthesized by deacetylation of chitin (poly-N-acetyl-D-glucosamine) to eliminate acetyl groups on the nitrogen atom by hydrolysis. The resulting polymer has a plurality of repeating units (e.g., about 30 to about 3000 repeating units, about 60 to about 600 repeating units, or such other amount as may be desired for the chosen end use) some or all of which contain deacetylated amino groups (e.g., about 30 to about 100% or about 60 to about 95% of the total repeating units), with the remaining repeating units (if any) containing acetylated amino groups. The polymer is cationic and may be regarded as being composed from glucosamine monomers. The chitosan may have a variety of number average molecular weights, e.g., about 5 to about 2000 kDa, about 10 to about 500 kDa, or about 10 to about 100 kDa. The chitosan may for example be an ultralow molecular weight material having a number average molecular weight less than about 50 kDa, a low molecular weight material having a number average molecular weight of about 50 to about 200 kDa, a medium molecular weight material having a number average molecular weight of about 200 to about 500 kDa or a high molecular weight material having a number average molecular weight greater than about 500 kDa. Chitosan derivatives may also be employed, for example derivatives in which one or more hydroxyl or amino groups have been modified for the purpose of altering the solubility or mucoadhesion characteristics of the derivative. Exemplary derivatives include thiolated chitosans, and non-thiolated chitosan derivatives such as acetylated, alkylated or sulfonated chitosans (for example O-alkyl ethers, O-acyl esters, cationized trimethyl chitosans and chitosans modified with polyethylene glycol). Chitosan derivatives may be obtained from a variety of sources. For example, thiolated chitosans may be obtained from ThioMatrix Forschungs Beratungs GmbH and Mucobiomer Biotechnologische Forschungs-und Entwicklungs GmbH or prepared by reaction of chitosan with a suitable thiolated reactant, e.g., as described in Published PCT Application No. WO 03/020771 A1 and in Roldo et al., Mucoadhesive thiolated chilosans as platforms for oral controlled drug delivery: synthesis and in vitro evaluation, European Journal of Pharmaceutics and Biopharmaceutics, 57, 115-121 (2004), Krauland et al., Viscoelastic Properties of a New in situ Gelling Thiolated Chitosan Conjugate, Drug Development And Industrial Pharmacy, 31, 885-893 (2005), Bernkop-Schnürch, Thiomers: A new generation of mucoadhesive polymers, Advanced Drug Delivery Reviews, 57, 1569-1582 (2005) and Bernkop-Schnürch et al., Thiomers: Preparation and in vitro evaluation of a mucoadhesive nanoparticulate drug delivery system, International journal of Pharmaceutics, 317, 76-81 (2006). The chitosan desirably is obtained in particulate form, for example, as free-flowing granules whose average particle diameter is less than about 1 mm, less than about 100 μm, about 1 to about 80 m, or less than 1 μm.
Sources for and types of other polysaccharides (for example, agars, alginates, carrageenans, chitins, chondroitin sulfates, dextrans, galactomannans, glycogens, hyaluronic acids, starches) may be chosen by persons skilled in the art based on selection characteristics similar to those given above for celluloses and chitosans. When combined in a mixture, the amounts of each polysaccharide may be varied widely to attain a desired combination of properties. For example, by altering the ratio of two polysaccharides in a blend, the biodegradable or bioresorbable characteristics and residence time of the blend may be altered. A mixture of two polysaccharides may for example contain about 99 to about 1% of the first polysaccharide and about 1 to about 99% of the second polysaccharide, or about 80 to about 20% of the first polysaccharide and about 20 to about 80% of the second polysaccharide, or about 60 to about 40% of the first polysaccharide and about 40 to about 60% of the second polysaccharide. Through appropriate selection of the types and amounts of polysaccharides in a mixture, rehydratable gels and sponges with tunable properties may be obtained. For example, a blend of CMC and chitosan may have good bacteriostatic performance due to the chitosan and controlled, sustained and tunable degradation rates due to the CMC, whereas chitosan used alone may form a gel or sponge having inherently poor mechanical and resorbtive properties and CMC used alone may form a gel or sponge lacking bactericidal properties.
The disclosed rehydratable gel composition and sponge are substantially collagen-free. Desirably the rehydratable gel composition and sponge are sufficiently free of collagen (e.g., containing no collagen at all) so as to be saleable worldwide for use without restriction in humans.
The disclosed rehydratable gel composition and sponge optionally are crosslinked before being packaged and sent to end users. Crosslinking preferably is carried out using a dehydrothermal crosslinking process. For the disclosed rehydratable gel this preferably is done by dehydrothermally crosslinking a mass of free-flowing rehydratable polysaccharide particles to form free-flowing rehydratable crosslinked polysaccharide particles. In other words, the particles preferably are themselves individually crosslinked while still remaining free-flowing and capable of later rapid dissolution and rehydration. For the disclosed sponge, crosslinking preferably is done by dehydrothermally crosslinking a shaped porous article which has been made by placing a solution of the desired polysaccharide in a suitable mold and lyophilizing the solution to form a porous solid having a shape corresponding to the desired uncompressed sponge shape. In other words, the sponge preferably is shaped and made porous prior to crosslinking.
Dehydrothermal crosslinking is in effect a solid state crosslinking process in which a material is exposed to one or both of heat and reduced pressure to cause initial dehydration followed by loss of additional water and formation of crosslinking bonds via an inter- or intra-molecular condensation process. It is not necessary to add external cross-linking agents, and in the case of the disclosed particles the presence of such agents could make it difficult to retain their free-flowing nature. Dehydrothermal crosslinking desirably involves dehydrating the product to be crosslinked to a moisture content less than about 1%, and using sufficient additional heat or vacuum to achieve a desired crosslink density. For example, in the absence of vacuum, temperatures above about 80° C., above about 90° C., above about 100° C. or above about 120° C. may be employed, with higher temperatures generally providing faster reaction rates. The polysaccharide desirably is not heated to an extent sufficient to cause browning, and accordingly temperatures less than 160° C. or less than 150° C. are preferred. Fairly long heating times may be needed at ambient pressure, for example, about 40 hours at 140-150° C. plus about total 20 hours for warmup and cooldown. When reduced pressure is used, lower temperatures may be employed and a pressure of at most about 1 mm Hg, and preferably at most about 10−3 mm Hg may be preferred. Thus the higher the temperature, the lower the required vacuum or beating time required to arrive at a given crosslink density, and vice versa. It is accordingly difficult to specify an exact heating time or range of heating times, although times of at least about 10 hours, at least about 20 hours, at least about 30 hours or about 40 to about 60 hours (not counting the times required for warmup and cooldown) may be employed. In many cases it will suffice to determine the heating time, temperature and pressure empirically, for example by using the Gel Retention Time test shown in the Examples to evaluate whether an appropriate degree of crosslinking has been obtained. For an uncrosslinked sample, the Gel Retention Time may for example be 1 day or less, whereas by using an appropriate degree of dehydrothermal crosslinking the Gel Retention Time may for example be extended to at least 2 days and preferably about 3 to about 7 days. The uncrosslinked sample may also tend to rehydrate less rapidly, absorb more water or form a more viscous gel or paste than its dehydrothermally crosslinked counterpart. In comparison to a conventionally crosslinked material ground into powder form, dehydrothermally crosslinked particles may be non-comminuted, may be crosslinked due to a condensation reaction (e.g., a dehydration reaction leading to the loss of water, or a reaction leading to the loss of another small molecule such as hydrogen chloride, methanol or acetic acid) rather than due to other crosslinking reactions (e.g., reactions involving addition polymerization (e.g. of vinyl groups), ionic reactions, or reactions involving sulfide or amine groups). In comparison to a conventionally crosslinked material ground into powder form, dehydrothermally crosslinked particles may also have a narrower polydispersity index, lower number average molecular weight, the capability to undergo further crosslinking, lower production costs and lower manufacturing capital requirements.
When two or more polysaccharides are employed to make the disclosed rehydratable gel, the dehydrothermal crosslinking process may be performed on one or on more than one of the polysaccharides before the particles have been blended. This permits customization of properties such as gelation behavior, gelation time and degradation time following implantation, by varying properties including the crosslinking time, temperature or vacuum for each polysaccharide component followed by blending of the crosslinked (or if desired, uncrosslinked) components after completion of the dehydrothermal crosslinking reaction(s) on the individual blend components. If desired, the resulting blend may be subjected to an additional dehydrothermal crosslinking reaction. The particles could also be kept separate and later mixed by an end user, although this will normally be less convenient than forming the mixture at a manufacturing site.
Dehydrothermal crosslinking conditions for the disclosed sponges are similar to those which may be employed for the polysaccharide particles. When two or more polysaccharides are employed to make the disclosed sponge, a mixture of the polysaccharides may be formed in solution, lyophilized and dehydrothermally crosslinked. As another approach, one or more of the polysaccharides in such a mixture may be dehydrothermally crosslinked, and the remaining polysaccharide(s) in such mixture may be imbibed into the dehydrothermally crosslinked polymer and the resulting swelled article may be lyophilized to form a sponge. These and other related approaches can permit differing degrees of property customization.
The disclosed rehydratable gel composition and sponge typically will be subjected to sterilization and placed in suitable sealed packaging (for example, a syringe, vial or bag made of a suitable material) prior to shipment to an end user. Additional property customization may be carried out by using a sterilization procedure such as gamma radiation or electron beam (E-Beam) processing to cause controlled chain scission. Cold ionizing radiation sterilization (e.g., cold E-Beam sterilization) may be employed to limit the degree of chain scission, as discussed in International Application No. PCT/US2009/041593 (corresponding to International Publication No. WO 2009/132229 A2), filed even date herewith.
The disclosed rehydratable gel composition and sponge may be rehydrated prior to placement or insertion in a treatment site, or may be placed while in a dry state and then rehydrated in silu (e.g., via the addition of an externally-supplied rehydrating fluid, by the uptake of endogenous fluids, or both). Rehydrating the sponge normally is relatively straightforward, and may be carried out by immersing or saturating the sponge with water or an aqueous solution containing any other desired ingredients. For example, normal saline solution may be a preferred and readily available rehydration solution, and other materials such as phosphate buffered saline (PBS) may be used if desired. Rehydrating the rehydratable gel particles may as noted above present additional difficulties due to the tendency of some dry powdered materials to form clumps when combined with water. Clumping may however be avoided by dispersing the rehydratable gel particles in a biocompatible water-miscible polar dispersant, followed by mixing the dispersion with sufficient aqueous particle solvent (viz., a water-based solvent for the particles) to convert the particles to a cohesive hydrogel. The dispersant is a thus a sufficiently poor solvent for the particles so that the mixture of particles and dispersant will not form a true solution. The particles in such a dispersion desirably are sufficiently small so that the dispersion is stable or quasi-stable (e.g., a colloidal dispersion or a reasonably persistent suspension) after the particles and dispersant have been agitated, e.g., by swirling them together. Without being bound by theory, the addition of the aqueous particle solvent is believed to permit rehydration to occur approximately simultaneously at the surface of each suspended particle via dissolution of the surrounding dispersant into the aqueous particle solvent phase, thereby permitting formation of a cohesive hydrogel without forming visible clumps of unhydrated polysaccharide. In this fashion a dispersed polysaccharide may be combined with water or an aqueous solution to form a clump-free hydrogel even though the dry powdered polysaccharide would not ordinarily do so. In many instances the disclosed method may be used to prepare a satisfactory clump-free gel using passage between two syringes, mild agitation or other simple mixing techniques without requiring the use of a mechanical stirrer. The disclosed mixing method may also permit formation of very concentrated hydrogels which could not be obtained by merely mixing a powdered polysaccharide with water or acidified water. The polysaccharide concentration typically will depend on the chosen molecular weight, and may for example be about 1 to about 20%, about 1 to about 10% or about 1 to about 5% of the rehydrated gel. The gel may desirably form in less than 30 minutes, less than 20 minutes, less than 10 minutes, less than 5 minutes, less than 1 minute or even essentially immediately after rehydration. For polysaccharides which do not immediately rehydrate, it may be desirable to saturate the powder and inject it before the polysaccharide has become too viscous to spray or otherwise dispense through a small orifice.
The selection of dispersant and aqueous particle solvent may depend upon the chosen polysaccharide. For polysaccharides such as chitosan which have relatively poor solubility in pure water but which become soluble when the water is acidified, deionized water may be used as the dispersant and acidified water may be used as the aqueous particle solvent. Other combinations of dispersant and aqueous solvent may also be used. For example, ethanol, isopropanol or acetone may be used as the dispersant for many polysaccharides (including chitosan and blends containing chitosan) and deionized water, normal saline solution or PBS may be used as the aqueous particle solvent.
The disclosed rehydratable gel particles may as noted above be crosslinked or uncrosslinked, and if crosslinked the crosslinking may be dehydrothermal crosslinking or crosslinking carried out using a separate crosslinking agent (for example, genipin, oxidized polysaccharide or glutaraldehyde). When crosslinked using a separate crosslinking agent, the resulting polymer may optionally be lyophilized and if need be comminuted to provide free-flowing particles.
The disclosed rehydratable gel composition and sponge may optionally include a variety of other ingredients before or after rehydration. Exemplary other ingredients include other solvents, acids, bases, buffering agents, antimicrobial agents, therapeutic agents and other adjuvants. An acid, base or buffering agent may for example maintain the gel at an appropriate pH for contacting human tissue, e.g., a pH greater than 5, a near-neutral pH, or a pH less than 8.5. Exemplary buffering agents include barbitone sodium, glycinamide, glycine, potassium chloride, potassium phosphate, potassium hydrogen phthalate, sodium acetate, sodium citrate, sodium phosphate and their conjugate acids.
The disclosed rehydratable gel composition and sponge desirably are inherently antimicrobial without requiring addition of a separate antimicrobial agent. A separate antimicrobial agent may be employed if desired. A useful list of such antimicrobial agents may be found, for example, in the above-mentioned U.S. Patent Application Publication No. US 2007/0264310 A1.
Exemplary therapeutic agents which may be employed in the disclosed rehydratable gel composition and sponge include any material suitable for use at the intended treatment site including analgesics, anti-cholinergics, anti-fungal agents, antihistamines, steroidal or non-steroidal anti-inflammatory agents, anti-parasitic agents, antiviral agents, biostatic compositions, chemotherapeutic/antineoplastic agents, cytokines, decongestants, hemostatic agents (e.g., thrombin), immunosuppressors, mucolytics, nucleic acids, peptides, proteins, steroids, vasoconstrictors, vitamins, mixtures thereof, and other therapeutic materials that will be known to those skilled in the art. A useful list of such therapeutic agents may be found, for example, in the above-mentioned U.S. Patent Application Publication No. US 2007/0264310 A1.
Other adjuvants that may be included in the disclosed rehydratable gel composition and sponge include dyes, pigments or other colorants (e.g., FD & C Red No. 3, FD & C Red No. 20, FD & C Yellow No. 6, FD & C Blue No. 2, D & C Green No. 5, D & C Orange No. 4, D & C Red No. 8, caramel, titanium dioxide, fruit or vegetable colorants such as beet powder or beta-carotene, turmeric, paprika and other materials that will be known to those skilled in the art); indicators; flavoring or sweetening agents including but not limited to anise oil, cherry, cinnamon oil, citrus oil (e.g., lemon, lime or orange oil), cocoa, eucalyptus, herbal aromatics (e.g., clove oil, sage oil or cassia oil), lactose, maltose, menthol, peppermint oil, saccharine, sodium cyclamate, spearmint oil, sorbitol, sucrose, vanillin, wintergreen oil, xylitol and mixtures thereof; antioxidants; antifoam agents; and theology modifiers including thickeners and thixotropes. The disclosed rehydratable gel composition and sponge desirably do not contain ingredients which might potentially harm patient tissues or structures, e.g., mucosal tissues in the nasal or sinus cavities.
In those instances where it is desirable to remove water from tissue, e.g., to remove fluid from polyps or edematous tissue, a hyperosmolar agent may be employed in the disclosed rehydratable gel composition and sponge. Exemplary hyperosmolar agents include furosemide, sodium chloride gel and other salt preparations that draw water from tissue or substances which directly or indirectly change the osmolar content of the mucous layer. Where sustained release or delayed release of a therapeutic agent is desirable, a release agent modifier may also be included.
The disclosed rehydratable gel composition and sponge may desirably be used as a part of a multi-step treatment regimen which disrupts a bacterial biofilm and discourages its return. For example, a series of steps that may be broadly classified as Cleansing/Disrupting, Killing, Aerating, Protecting/Coating, and Healing may be carried out. The Cleansing/Disrupting step may be carried out by administering a solvating system as discussed above in connection with
The invention is further illustrated in the following non-limiting examples.
Powdered sodium carboxymethylcellulose (CMC 52MSC from Emerging Technologies, Inc.) was combined with 1% titanium dioxide and dehydrothermally crosslinked by warming to 140° C. over 10 hours, heating at 150-160° C. for 40 hours, and cooling to ambient temperature over 10 hours. A free-flowing, white powder with an average particle diameter of about 40 μm was obtained. The powder was packaged in 1.5 gram portions in polyurethane pouches and E-Beam sterilized at 30 kGy.
A 0.7 g portion of the Example 1 CMC powder was combined with 3 mL deionized water in a 10 mL LUER-LOK™ syringe (from Becton, Dickinson and Co.). The syringe was connected to a second such 10 mL syringe using a LUER™ connector (from Becton, Dickinson and Co.) and the syringe plungers were alternately depressed in an effort to rehydrate the powder. A poorly-mixed mass containing many clumps was obtained, and the clumps occluded the passage between the syringes. In a second run, a 0.7 g portion of the Example 1 CMC powder was combined with 0.5 mL ethanol and shaken, resulting in an apparently stable suspension. A 3 mL portion of deionized water in the second syringe was added to the suspension and then the syringe plungers were alternately depressed to mix the ingredients, resulting in the gradual formation of a clear, homogenous hydrogel which was completely free of visible unhydrated CMC particles. The hydrogel could readily be injected through a 2.7 mm inside diameter, 10 cm long cannula onto a target surface, resulting in a thick, highly viscous uniform gel with no noticeable clumps. The gel looked somewhat like an amorphously-shaped sponge.
Samples of the Example 2 gel were placed between collagen-coated pins in an MTS tensile testing machine (MTS Systems Corp.), and evaluated at a separation rate of 25.4 mm/min to determine tensile adhesive strength for the gel-collagen bond. A value of about 55 kPa was obtained, whereas only about 35 kPa was obtained using a gel made with uncrosslinked CMC powder.
A 1.5 g portion of the Example 1 powder was rehydrated to form a clump-free gel using the method of Example 2. The gel was submerged in 200 mL PBS, then poured onto a 150 μm sieve, allowed to drain and weighed. The gel was returned to the collected PBS solution, stored overnight and the sieve and reweighing procedure repeated for a total of three times at which point the gel had disappeared. The resulting 3 day test duration was recorded as the Gel Retention Time. A gel made from the Example 1 CMC powder without dehydrothermal crosslinking had a Gel Retention Time of less than 1 day.
High molecular weight powdered chitosan obtained from crab shells (BIOCHEMICA™ high viscosity chitosan from Sigma-Aldrich Co.) was suspended in deionized water at addition levels of 10, 25 and 50 g/L. A stirred 50 mL portion of each suspension was titrated with 1M HCl. As shown in
In a separate run, a 1% solution of the high molecular weight chitosan was formed by adding the chitosan powder to deionized water containing 1% acetic acid. The solution had a 453 cP viscosity when evaluated at 37° C. using a BROOKFIELD™ DV-II+ Pro cone and plate viscometer equipped with a CP-52 cone spindle. A similarly-prepared 1% solution of low molecular weight chitosan (BIOCHEMICA low viscosity chitosan from Sigma-Aldrich Co.) had a 185 cP viscosity.
Using the method of Example 1, low and high molecular weight powdered chitosan was dehydrothermally crosslinked at 90° C. for 10 hours or at 120° C. for 20 hours, added to varying amounts of 1M HCl to form gels and evaluated for adhesion using the method of Example 3.
In a separate run, medium molecular weight chitosan was dehydrothermally crosslinked at 120° C. for 40 hours using the method of Example 1 and evaluated for adhesion using the method of Example 2. A value of about 65 kPa was obtained, whereas only about 41 kPa was obtained using a gel made with uncrosslinked CMC powder.
In a series of runs, powdered chitosan (ultralow molecular weight chitosan oligosaccharide lactate, or BIOCHEMICA™ low or medium viscosity crab shell chitosan, all from Sigma-Aldrich Co.) was employed by itself, in a blend of chitosans, or in a blend with the Example 1 powdered CMC, and mixed with water acidified with varying amounts of HCl or acetic acid. The resulting mixtures were stirred for five minutes using a powered stirrer. Doing so enabled the antimicrobial testing described below, but would be much less convenient if required to be performed prior to surgery. The stirred solutions were evaluated to determine the antimicrobial activity of the resulting gels versus E. Coli, S. Aureus, P. Aeruginosa and in some instances S. Pneumoniae. The antimicrobial activity evaluation used a modified zone of inhibition plate procedure, in which a small quantity of the gel was streaked across agar plates which had been freshly streaked with the desired microbe. Unlike a traditional zone of inhibition test, in which an antibiotic-soaked paper disk is placed against the agar surface and the antibiotic diffuses outwardly through the agar, the viscous nature of the gel discouraged such diffusion. The results were thus somewhat Boolean in nature, and mainly provided an indication as to whether or not inhibition had occurred. The results are shown below in Table 1.
TABLE 1
Antimicrobial Activity Evaluation
Chitosan
Run
(amount and
CMC
Microbial Inhibition
No.
type)
(amount)
Acidification1
E. Coli
S. Aureus
P. Aeruginosa
S. Pneumoniae
1
100% LMW2
pH 4.5
Yes
Yes
Yes
2
100% LMW
pH 6
No
Mild
No
3
100% MMW3
pH 4.5
No
No
No
4
100% MMW
pH 6
No
Mild
No
5
20% LMW
80%
pH 4.5
Yes
Yes
Yes
64
20% LMW
80%
pH 4.5
Yes
Yes
Yes
7
40% LMW
60%
pH 4.5
Yes
Yes
Yes
8
60% LMW
40%
pH 4.5
Yes
Yes
Yes
9
80% LMW
20%
pH 4.5
Yes
Yes
Yes
104
80% LMW
20%
pH 4.5
Yes
Yes
Yes
11
20% LMW
80%
pH 5
Yes
Yes
Yes
12
40% LMW
60%
pH 5
Yes
Yes
Yes
13
60% LMW
40%
pH 5
Yes
Yes
Yes
14
80% LMW
20%
pH 5
Yes
Yes
Yes
15
20% LMW
80%
pH 5.5
Yes
Yes
Yes
16
40% LMW
60%
pH 5.5
Yes
Yes
Yes
17
60% LMW
40%
pH 5.5
Yes
Yes
Yes
18
80% LMW
20%
pH 5.5
Yes
Yes
Yes
19
20% LMW
80%
0.1% acetic acid
Yes
Yes
Yes
Yes
20
20% LMW
80%
0.12% acetic acid
Yes
Yes
Yes
Yes
21
20% LMW
80%
0.14% acetic acid
Yes
Yes
Yes
Yes
22
20% LMW
80%
0.16% acetic acid
Yes
Yes
Yes
Yes
23
20% LMW
80%
0.18% acetic acid
Yes
Yes
Yes
Yes
24
20% LMW
80%
0.2% acetic acid
Yes
Yes
Yes
Yes
25
20% LMW
80%
0.2% acetic acid
Yes
Yes
Yes
Yes
26
20% LMW
80%
0.2% acetic acid
No
No
No
No
27
50% LMW
50%
0.2% acetic acid
Yes
Yes
Yes
Yes
28
20% LMW +
5%
0.2% acetic acid
Yes
Yes
Yes
Yes
75% MMW
29
20% LMW +
pH 5
Yes
Yes
Yes
80% MMW
30
10% LMW +
pH 5
Yes
Yes
Yes
90% MMW
31
5% LMW +
pH 5
Yes
Yes
Yes
95% MMW
32
3% LMW +
pH 5
Yes
Yes
Yes
97% MMW
33
2% LMW +
pH 5
Yes
Yes
Yes
98% MMW
34
1% LMW +
pH 5
Yes
Yes
Yes
99% MMW
35
0.5% LMW +
pH 5
Yes
Yes
Yes
99.5% MMW
36
100% MMW
pH 5
Yes
Yes
Yes
37
100% ULMW5
pH 5
Yes
Yes
Yes
Yes
1The indicated pH values are the pH at the start of rehydration, as obtained using HCl. Where acidification was performed using acetic acid, the amount of added acid is shown.
2“LMW” is low molecular weight chitosan.
3“MMW” is medium molecular weigh chitosan.
4Gel sample aged 48 hours prior to microbial inhibition test.
5“ULMW” is ultralow molecular weigh chitosan.
The results in Table 1 show that chitosan and blends of chitosan with the polysaccharide carboxymethylcellulose may be rehydrated to provide gel layers with inherent antimicrobial properties.
A free-flowing crosslinked powder may be prepared by dissolving a dry powdered polysaccharide polymer such as carboxymethyl chitosan in water to produce a viscous solution containing about 5 wt. % polymer. A crosslinker solution containing 10 wt. % dialdehyde starch or 0.1 wt. % glutaraldehyde may be quickly mixed with the polymer solution by placing each solution in a 10 mL LUER-LOK™ syringe (from Becton, Dickinson and Co.), connecting the syringes to one another using a LUER™ connector (from Becton, Dickinson and Co.) and alternately depressing the syringe plungers to exchange the fluids between the two syringes several times. After a short dwell period during which crosslinking takes place, a cohesive gel should be obtained. The gel may be converted to particles by freezing and lyophilize the frozen gel, followed by grinding the lyophilization product.
A free-flowing crosslinked powder may also be prepared by soaking a dry powdered polysaccharide polymer in a nonsolvating liquid crosslinking agent or nonsolvating crosslinker solution. The dry powdered carboxymethyl chitosan starting material used in Example 8 may be soaked in ethylene glycol diglycidyl ether (e.g., E27203 ethylene glycol diglycidyl ether from Sigma-Aldrich) for sufficient time to permit crosslinking to occur. The resulting mass of free-flowing, crosslinked particles may be washed with methanol to remove residual crosslinking agent and dried using gentle heat. Depending on the chosen polysaccharide, a variety of crosslinkers may be employed. For example, ethylene glycol diglycidyl ether may be replaced with hexamethylene diglycidyl ether or other glycidyl crosslinker reactive towards hydroxyl or amine groups. If the polysaccharide contains primary amine groups, appropriately reactive crosslinkers such as dialdehyde starch, oxidized methyl cellulose or glutaraldehyde may be employed.
Equal volumes of a 2.5 wt. % solution of carboxymethyl chitosan in PBS and 10 wt. % dialdehyde starch were quickly mixed using two 3 mL syringes like the 10 mL syringes described in Example 8. The resulting cohesive hydrogel was expelled from the back of the syringes to provide a mass that maintains its shape.
Equal volumes of a 5 wt. % solution of carboxymethyl chitosan in PBS were crosslinked via E-beam radiation both when frozen and at room temperature. The resulting hydrogels were lyophilized into readily powderable sponges. When placed in PBS, the sponges persisted for three to seven days.
In addition to a composition comprising free-flowing rehydratable particles of substantially collagen-free dehydrothermally crosslinked polysaccharide, other embodiments of the invention include like compositions:
In addition to an implantable article comprising a rehydratable porous sponge comprising substantially collagen-free dehydrothermally crosslinked polysaccharide; other embodiments of the invention include like articles:
In addition to a method for making a polysaccharide gel-forming composition, which method comprises:
In addition to a method for making an implantable article, which method comprises:
In addition to a method for treating mucosal tissue and other body structures, which method comprises applying thereto a gel or sponge comprising rehydrated substantially collagen-free dehydrothermally crosslinked polysaccharide, other embodiments of the invention include like methods:
In addition to a method for converting a dry powdered composition to a gel, which method comprises:
Although specific embodiments have been illustrated and described herein for purposes of description of the preferred embodiments, it will be appreciated by those of ordinary skill in the art that a wide variety of alternate or equivalent implementations calculated to achieve the same purposes may be substituted for the specific embodiments shown and described without departing from the scope of the present invention. This application is intended to cover any adaptations or variations of the preferred embodiments discussed herein. Therefore, it is manifestly intended that this invention be limited only by the claims and the equivalents thereof.
Hissong, James Britton, Oliver, Dana A., Myntti, Matthew F., Medina, Jennifer G., Vaccaro, Brian J.
| Patent | Priority | Assignee | Title |
| 10786596, | Jan 12 2018 | Boston Scientific Scimed, Inc. | Powder for achieving hemostasis |
| 11701448, | Jan 12 2018 | Boston Scientific Scimed, Inc. | Powder for achieving hemostasis |
| Patent | Priority | Assignee | Title |
| 3184385, | |||
| 3678931, | |||
| 3914214, | |||
| 3989044, | Aug 11 1975 | Warner-Lambert Company | Syringe |
| 4604384, | Jun 24 1982 | Pharmaceutical gel composition | |
| 4659700, | Mar 02 1984 | JOHNSON & JOHNSON MEDICAL INC | Chitosan-glycerol-water gel |
| 4895724, | Jun 07 1985 | Pfizer Inc | Chitosan compositions for controlled and prolonged release of macromolecules |
| 4960413, | May 19 1987 | The Shirley Institute | Wound dressing |
| 4983385, | Sep 29 1988 | Sunstar Kabushiki Kaisha; WYETH KABUSHIKI KAISHA | Ointment base |
| 5308546, | Dec 09 1991 | Glow-Tec | Phosphorescent toy gel composition and methods of manufacture |
| 5312324, | Sep 15 1992 | Nasal dressing system | |
| 5318780, | Oct 30 1991 | MDV TECHNOLOGIES, INC | Medical uses of in situ formed gels |
| 5550189, | Apr 17 1992 | Kimberly-Clark Worldwide, Inc | Modified polysaccharides having improved absorbent properties and process for the preparation thereof |
| 5623064, | Dec 01 1993 | Marine Polymer Technologies | Poly-β-1→-4-N-acetylglucosamine |
| 5667778, | Apr 30 1993 | CHILDREN S MEDICAL CENTER CORPORATION; Massachusetts Institute of Technology | Injectable bladder muscle cells-polymer suspension for treatment of vesicoureteral reflux and incontinence |
| 5676964, | May 13 1988 | Fidia, S.p.A. | Crosslinked carboxy polysaccharides |
| 5679658, | May 08 1995 | Chitogenics, Inc. | N,O-carbonxymethylchitosan for prevention of surgical adhesions |
| 5688522, | Mar 23 1993 | KCI USA, INC | Ointment for wound treatment |
| 5723144, | Mar 23 1993 | KCI USA, INC | Ointment for wound treatment |
| 5747475, | Apr 04 1995 | IMMUNOPHOTONICS, INC | Chitosan-derived biomaterials |
| 5770712, | Mar 14 1997 | FORMAN, MR BARRY | Crosslinked hydrogel beads from chitosan |
| 5820608, | Sep 29 1993 | Boston Scientific Scimed, Inc | Method for in vivo chemically triggered disintegration of medical device |
| 5836970, | Aug 02 1996 | The Kendall Company | Hemostatic wound dressing |
| 5840341, | Aug 20 1994 | Archimedes Development Limited | Drug delivery composition containing chitosan or derivative thereof having a defined z. potential |
| 5993846, | Aug 13 1993 | Pharmos Corporation | Bioadhesive emulsion preparations for enhanced drug delivery |
| 6051648, | Dec 18 1995 | AngioDevice International GmbH | Crosslinked polymer compositions and methods for their use |
| 6096018, | Sep 29 1993 | Boston Scientific Scimed, Inc | Medical treatment utilizing ionically crosslinked medical devices |
| 6123965, | Jan 26 1996 | PEROSPHERE INC | Methods and compositions for enhancing the bioadhesive properties of polymers |
| 6224893, | Apr 11 1997 | Regents of the University of Colorado, The | Semi-interpenetrating or interpenetrating polymer networks for drug delivery and tissue engineering |
| 6290712, | Apr 04 1995 | IMMUNOPHOTONICS, INC | Laser/sensitizer assisted immunotherapy |
| 6320029, | Dec 01 1995 | The American National Red Cross; Coalition for Hemophilia B, Inc. | Methods of production and use of liquid formulations of plasma proteins |
| 6334968, | May 22 1996 | Ben Gurion University of the Negev | Method of forming polysaccharide sponges for cell culture and transplantation |
| 6342251, | Dec 02 1997 | Archimedes Development Limited | Compositions for nasal administration |
| 6344488, | Aug 04 1997 | SMITH & NEPHEW ORTHOPAEDICS AG | Temperature-controlled pH-dependent formation of ionic polysaccharide gels |
| 6346272, | Aug 07 1990 | MDV TECHNOLOGIES, INC | Body cavity drug delivery with thermo-irreversible polyoxyalkylene and ionic polysaccharide gels |
| 6417347, | Aug 24 2000 | Boston Scientific Scimed, Inc | High yield S-nitrosylation process |
| 6458889, | Dec 18 1995 | AngioDevice International GmbH | Compositions and systems for forming crosslinked biomaterials and associated methods of preparation and use |
| 6514522, | Apr 08 1998 | Chondros, Inc. | Polymer constructs |
| 6545042, | Nov 05 1996 | GP Medical | Acellular biological material chemically treated with genipin |
| 6566406, | Dec 04 1998 | Incept LLC | Biocompatible crosslinked polymers |
| 6599627, | Dec 13 2000 | Purdue Research Foundation | Microencapsulation of drugs by solvent exchange |
| 6602952, | Jun 11 1999 | Nektar Therapeutics | Hydrogels derived from chitosan and poly(ethylene glycol) or related polymers |
| 6632423, | Mar 14 2000 | Novartis AG | Viscoelastics for use in middle ear surgery |
| 6664301, | Feb 20 2002 | POLY-GEL L L C | Method for using glycol additives to texturally modify natural gum hydrogels |
| 6706690, | Jun 10 1999 | Baxter International Inc; BAXTER HEALTHCARE S A | Hemoactive compositions and methods for their manufacture and use |
| 6719987, | Apr 16 2001 | NUCRYST PHARMACEUTICALS CORP | Antimicrobial bioabsorbable materials |
| 6806260, | Nov 10 1998 | Netech, Inc. | Functional chitosan derivative |
| 6809085, | May 20 1999 | Chitogenics, Inc. | Adherent N,O-Carboxymethylchitosan drug delivery devices for moist tissue and methods of their use |
| 6835389, | Aug 26 1998 | Teijin Limited | Powder Composition for nasal administration |
| 6989373, | Nov 15 2000 | SMITH & NEPHEW ORTHOPAEDICS AG | Method for restoring a fat-pad |
| 6991652, | Jun 13 2000 | Clemson University Research Foundation | Tissue engineering composite |
| 7053068, | Aug 31 2001 | MUCOBIOMER BIOTECHNOLOGISCHE FORSCHUNGS-UND ENTWICKLUNGS GESMBH | Chitosan-thio-amidine conjugates and their cosmetic as well as pharmaceutic use |
| 7070582, | Aug 09 2002 | Boston Scientific Scimed, Inc | Injection devices that provide reduced outflow of therapeutic agents and methods of delivering therapeutic agents |
| 7087249, | Apr 23 2001 | NUCRYST PHARMACEUTICALS CORP | Treatment of mucosal membranes |
| 7098194, | Nov 15 2001 | SMITH & NEPHEW ORTHOPAEDICS AG | Composition and method to homogeneously modify or cross-link chitosan under neutral conditions |
| 7125860, | Aug 31 2000 | FIDIA FARMACEUTICI S P A | Cross-linked derivatives of hyaluronic acid |
| 7195675, | Oct 08 2002 | Ricom Corporation | Chitosan-containing polysaccharide, method for preparing the same and use thereof |
| 7229966, | Dec 17 2002 | MDRNA, INC | Compositions and methods for enhanced mucosal delivery of Y2 receptor-binding peptides and methods for treating and preventing obesity |
| 7354600, | Nov 04 1998 | Muco-adhesive polymers, use thereof and method for producing the same | |
| 7727547, | Apr 04 2000 | Tissuemed Limited | Tissue-adhesive formulations |
| 7834065, | Jan 31 2006 | BMG Incorporated | Medical-use two part reactive adhesive and medical-use resin having self-degradation property |
| 8802652, | Apr 24 2008 | Hitachi Displays, Ltd | Rehydratable polysaccharide particles and sponge |
| 9561248, | Apr 24 2008 | Medtronic, Inc. | Method for rehydrating polysaccharide particles |
| 20020042473, | |||
| 20020064580, | |||
| 20020193812, | |||
| 20030073663, | |||
| 20040029855, | |||
| 20040101548, | |||
| 20040127698, | |||
| 20040137041, | |||
| 20040157734, | |||
| 20040176477, | |||
| 20040219117, | |||
| 20050002893, | |||
| 20050019404, | |||
| 20050069572, | |||
| 20050096282, | |||
| 20050136122, | |||
| 20050176620, | |||
| 20050208122, | |||
| 20050238702, | |||
| 20050284809, | |||
| 20060054634, | |||
| 20060134185, | |||
| 20060147539, | |||
| 20060172000, | |||
| 20060234871, | |||
| 20060292030, | |||
| 20070020314, | |||
| 20070031467, | |||
| 20070031474, | |||
| 20070048291, | |||
| 20070066924, | |||
| 20070087059, | |||
| 20070098675, | |||
| 20070110788, | |||
| 20070191963, | |||
| 20070202142, | |||
| 20070243130, | |||
| 20070243131, | |||
| 20070264310, | |||
| 20080031854, | |||
| 20080069857, | |||
| 20080075657, | |||
| 20080317765, | |||
| 20080319101, | |||
| 20090005339, | |||
| 20090010982, | |||
| 20090016978, | |||
| 20090041814, | |||
| 20090062233, | |||
| 20090270346, | |||
| 20100291055, | |||
| CA2348842, | |||
| CA2574232, | |||
| CN1872351, | |||
| EP815879, | |||
| EP1228771, | |||
| EP1880738, | |||
| FR2889449, | |||
| JP2000095678, | |||
| JP2002327338, | |||
| JP2008247975, | |||
| JP2008285611, | |||
| JP7116241, | |||
| TOO2009028965, | |||
| WO40252, | |||
| WO100246, | |||
| WO3020771, | |||
| WO3057274, | |||
| WO3080135, | |||
| WO2004026200, | |||
| WO2006080523, | |||
| WO2007059390, | |||
| WO2007071375, | |||
| WO2008005671, | |||
| WO2008008857, | |||
| WO2008067655, | |||
| WO2008097317, | |||
| WO9216245, | |||
| WO9321906, | |||
| WO9614828, | |||
| WO9819718, | |||
| WO9831712, | |||
| WO9901166, | |||
| WO9907416, |
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